Cardioplegia delivery system

Abstract: A cardioplegia system for delivering cardioplegic solution to the heart during open heart surgery in cooperation with an extracorporeal blood circuit employing a heart/lung machine, includes a conduit (12) diverting a portion of the blood flow from the heart/lung machine to a cardioplegia delivery line (28). A heat exchanger (31) for controlling fluid temperature is provided in the cardioplegia delivery line. A first pump (30,26) combines the blood from the conduit with a second fluid (32) and delivers the combined flow into the delivery line (28) leading to the heat exchanger (31). A control panel (52) is operatively connected for adjusting the ratio of blood (14) and second fluid (32) delivered by the first pump (30,26) and for adjusting the total volumetric rate of flow from the first pump (30,26).

Description: TECHNICAL FIELD OF THE INVENTION This invention relates to fluid delivery systems, and more particularly to systems for the delivery of multiple fluids in a cardioplegia circuit to support a patient's heart during open heart surgery. BACKGROUND OF THE INVENTION In the performance of open heart surgery, the patient is supported by an extracorporeal blood circuit employing a heart/lung machine. The heart is isolated from the vascular system, and venous blood is diverted into the extracorporeal blood circuit where it is oxygenated, temperature-controlled and returned to the patient's arterial side. A separate circuit is established for supplying a cardioplegic solution to the heart as the surgery proceeds. The cardioplegia circuit functions to still the heart, lower the metabolic requirements of the heart, protect the heart during periods of ischemia, and, finally, prepare the heart for reperfusion at the end of the procedure. Operation of the extracorporeal blood circuit as well as the cardioplegia delivery is performed by a trained perfusionist under the direction of the surgeon. The principal elements of cardioplegia solution are blood, representing a small fraction diverted from the output of the heart/lung machine, combined with a crystalloid solution. In addition, a minor but critical amount of potassium solution is added to the cardioplegic flow to still the heart. Depending upon the requirements of the particular surgery, the cardioplegia solution may be cooled or warmed, and may be delivered in antegrade fashion to the aortic root or coronary ostia, or in a retrograde mode to the coronary sinus. The requirements placed upon the cardioplegic solution vary as the surgery proceeds, and are subject to the clinical judgment of individual surgeons. A typical cardioplegia delivery system employs two tubes routed through a single rotary peristaltic pump to forward both the separate blood and crystalloid solutions to a Y combining the two into a single flow. The ratio between the blood and crystalloid solution is determined simply by the relative diameters of the tubing carrying the two solutions, since each is mounted on the same rotary peristaltic mechanism and thus is forwarded by the same action. The tubing is usually provided in a 4:1 ratio of blood to crystalloid cross-sectional flow area, so that the rotary peristaltic pump is delivering blood and crystalloid to the delivery line in a ratio of approximately 4:1. Potassium is typically provided to the delivery line upstream of the pump from two alternate crystalloid solutions containing potassium, one having a relatively low concentration of potassium, the other a higher concentration. The perfusionist selects between the two sources as monitoring of the patient's condition indicates. The higher potassium concentration is utilized to arrest the heart, while the lower is used to maintain the stilled condition. The clinical team must provide sufficient potassium in the cardioplegia solution to establish the stilled condition of the heart and maintain it during the procedure, while avoiding the risks associated with hyperkalemia which may result from excessive potassium. Existing systems for delivery of cardioplegia are characterized by poor adaptability to varying requirements which the surgeon in charge may place upon the system as to ratios of the principal ingredients in the cardioplegia flow and as to temperature control. The systems have particularly poor control over the cardioplegia delivery at low flow rates. Moreover, the shearing forces to which the blood in the cardioplegia line is subjected by peristaltic action risks damage to the blood. EP-A-0 445 079 is directed to a cardioplegia delivery system which includes a first pump and a second pump. The first pump draws a first fluid (i.e., crystalloid) from a line and a second fluid (i.e., blood) from a line for mixing at point. The system mixes the two fluids at a ratio of 4:1. The first pump pumps the fluid mixture to heat exchanger. The second pump (14) is not used to introduce an additional fluid to a patient delivery line; rather, the second pump circulates the fluid mixture through the heat exchanger and perfuses a patient through perfusion circuit. SUMMARY OF THE INVENTION The invention relates to a cardioplegia system as claimed in claim 1 or 10. In one embodiment the invention includes control means for adjusting the ratio of blood and second fluid delivered by the first pump, for adjusting the total volumetric rate of flow from the first pump, and for controlling the operation of the second pump so that the volumetric rate of flow of the third fluid is maintained at a selected percentage of the flow rate from the first pump. The first pump preferably employs two pumping chambers, so that one chamber may be refilled while the other is emptying, whereby substantially continuous flow from the first pump may be achieved. The second pump is preferably a positive displacement pump, either a syringe or a volumetric pouch configuration containing potassium solution driven at a rate controlled by the control means. The output of the second pump joins the delivery line downstream from the first pump. In a specific embodiment, the heat exchanger has the ability to both heat and cool the cardioplegic solution, and operates under the control of the control means. Preferably, the first pump includes at least one disposable in-line bladder and a separate drive means for changing the volume of the bladder. In the preferred embodiment, a fill cycle of the first pump comprises two separate time segments, including a first period for introduction of blood from the main extracorporeal blood circuit and a second period for the introduction of a second fluid, whereby the blood and the second fluid are combined in the bladder in a selected ratio before being forwarded from the first pump. Also preferably the pressure of the cardioplegia solution is sensed, monitored, and controlled by the control means within safe operating limits. According to another aspect of the invention, all of the major operating conditions of a cardioplegia system including the desired volumetric rates, the desired ratios and percentages of blood, second fluid, third fluid, and any additional fluids, the output temperature and heating and cooling of the output fluid as well as the appropriate operating pressures and safety pressure conditions for either antegrade or retrograde cardioplegia are conveniently controlled from a centralized operator control panel connected to the cardioplegia system through a microprocessor control section. This advantageously frees perfusionist, surgeons and other healthcare professionals performing delicate medical procedures, from the complex, cumbersome and sometimes confusing manual rigging, connecting, heating, cooling, monitoring and adjusting of all the various aspects of the prior cardioplegia systems. The centralized control results in increased safety and quality of cardioplegia fluid delivery. The system is easily adaptable and adjustable to the particular requirements of a given patient. The system may also be adaptable for blood fluid delivery for other clinical applications and healthcare procedures in which multifluid pumping systems may be desirable or beneficial. BRIEF DESCRIPTION OF THE DRAWINGS For a more complete understanding of the present invention and for further advantages thereof, reference is now made to the following Description of the Preferred Embodiments taken in conjunction with the accompanying Drawings in which: FIGURE 1 is a schematic diagram of a cardioplegic delivery system embodying the invention; FIGURE 2 is a plan view of a disposable pump cassette for a blood/crystalloid combining pump which may be used in the system of FIGURE 1; FIGURE 3 is a plan view of a pump mechanism for operation of the cassette of FIGURE 2; FIGURE 4 is a schematic illustration of the functioning of the two pump chambers of FIGURE 2; FIGURE 5 is a schematic illustration of one pump driver and associated valving mechanisms of the mechanism of FIGURE 3; and FIGURE 6 is a timing diagram illustrating the cycle of the blood/crystalloid pump depicted in FIGURES 2-5. DESCRIPTION OF THE PREFERRED EMBODIMENTS As depicted in Figure 1, a cardioplegia delivery system 10 is established to provide solution to the heart of a patient during open heart surgery. The principal component of the cardioplegic solution is blood delivered to the system through conduit 12 which is connected to the output of the oxygenator 14 of the heart/lung machine sustaining the patient's vascular system while the heart is isolated therefrom during surgery. Oxygenator 14 provides arterial blood in the main extracorporeal circuit through a return line 16 to the patient's aorta. A fraction, usually about 10%, of the heart/lung machine output is diverted into conduit 12 for processing by the cardioplegic circuit and forwarding to the patient's heart through cardioplegia delivery line 18. The cardioplegic solution flowing through line 18 may be delivered through antegrade line 20 to the aortic root, or through retrograde line 22 to the coronary sinus. A crystalloid solution is stored in container 24 for combination with blood flowing in line 12 in a disposable pumping cassette 26. The output of cassette 26 is supplied through line 28 to a heat exchanger 31. Pump cassette 26 is controlled by an electromechanical pump mechanism 30 in which cassette 26 is mounted. A second pump 32 containing potassium solution supplies its output to line 28 downstream from the pump cassette 26. Pump 32 may be a syringe pump or a volumetric pouch of a type well known in the infusion art. In the case where pump 32 is a syringe pump, the potassium solution may be loaded into a syringe, and the syringe mounted in pump 32 which progressively depresses the syringe plunger to deliver potassium solution to line 28. The flow rates of potassium solution are less than about 10%, and preferably less than about 5%, of the total flow rate issuing from pump cassette 26. An accurately controllable pump, such as a syringe pump, may be advantageously used in applications where a particular fluid additive or constituent must be a carefully controlled small portion, less than about 10%, of the total flow volume. In the heat exchanger 31, the cardioplegic solution is juxtaposed with a circulating temperature controlled fluid to adjust the temperature of the solution prior to forwarding the solution to the heart through line 18. Preferably pump 33 circulates temperature controlled fluid through the heat exchanger 31 either by push or pull. Figure 1 depicts a push through coolant system in which a pump 33 circulates the control fluid through heat exchanger 31 and then to a two-way valve 34, which valve 34 may direct the circulating fluid either to an ice bath 36 for cooling or a heated water reservoir 38 for heating. The circulating fluid is then pumped via valve 40 back through the heat exchanger 31 where the cardioplegia solution receives heating or cooling without contamination across a sealed heat transfer material or membrane within the heat exchanger 31. The system includes patient monitoring of myocardial temperature along the signal path 42 and heart pressure along signal path 44 communicating to a central microprocessor control section 46. In addition, the pressure and temperature of the cardioplegic solution in delivery line 18 is sensed and the data is forwarded along signal paths 48 and 50 to the control microprocessor 46. Data input to microprocessor 46 through control panel 52 may include an advantageous combination of the following parameters: 1. Desired overall volumetric flow rate through disposable pump cassette 26; 2. Desired blood/crystalloid ratio to be forwarded by disposable pump cassette 26. 3. Desired potassium concentration to be established by pump 32. 4. Desired temperature of solution in cardioplegia delivery line 18 or desired patient temperature. 5. Safety parameters such as the pressure of the cardioplegia solution in the system or in the patient. In response to the data input through the control panel 52 and the monitored conditions along signal paths 42, 44, 48 and 50, microprocessor control section 46 controls the operation of pump mechanism 30 via signal path 54, and of potassium syringe pump 32 by signal along path 56. In addition, microprocessor control section 46 controls the circulation of fluid in the heat exchanger circulation path along signal path 58 either for obtaining a desired patient temperature or a desired output solution temperature. Further, the safety parameters such as pressure limits for a particular procedure or a particular patient may be controlled based upon input settings or based upon preset standards, as for example, one range of acceptable pressure limits for antegrade and another range for retrograde cardioplegia. In accordance with the invention, the microprocessor controller section 46 controls the pump mechanism 30 to combine crystalloid from container 24 and blood from line 12 in any selected ratio over a broad range of blood/crystalloid ratios. The controller 46 may command the pump mechanism 30 to deliver blood without crystalloid addition. As an example, a preferred range for the blood/crystalloid ratio adjustment capability is from 0 to 20:1. The rate of flow produced by the pump mechanism 30 of the combined output from disposable pump cassette 26 is, for example, variable from 0 to 500 milliliters per minute. The pump mechanism 30 may be operated by microprocessor 46 in either a continuous or intermittent mode by instruction through control panel 52. The potassium syringe pump 32 is automatically controlled to deliver at a rate such that the introduction of potassium solution to line 28 is automatically maintained at the selected concentration vis-a-vis the flow of disposable cassette 26, without regard to changes requested in the flow rate from pump cassette 26 or changes in the blood/crystalloid ratio, requested of the pump mechanism 30 through microprocessor 46. Disposable pump cassette 26 is illustrated in Figure 2. The cassette may be formed from two flexible plastic sheets 60 bonded together selectively to form open flow paths and chambers therebetween. Each sheet 60 may be of any simple flexible material such as polyvinylchloride, and the sheets may be radio frequency welded together, leaving the flow paths and pump chambers unbonded. A bladder cassette of this type advantageously reduces the shearing forces and potential damage to which blood might be subjected in other pumps, such as peristaltic pumps. The entry side 62 of cassette 26 includes a blood inlet 64 and a crystalloid inlet 66. Inlets 64 and 66 lead to a common pump inlet path 68, which is bifurcated to form pump flow paths 70 and 72. Flow path 70 leads to enlarged fluid bladder pump chamber 74 and path 72 leads to an identical fluid bladder pump chamber 76. Outlet path 78 from pump chamber 74 and outlet path 80 from pump chamber 76 are joined at a common outlet 82 from cassette 26 for delivery of the mixed cardioplegic solution to line 28. Figure 2 depicts six valve sites located along the fluid paths in cassette 26. These are sites at which the corresponding flow path may be occluded through operation of a valve plunger on the pump mechanism 30, to press the sheets 60 together at the valve, when the cassette 26 is mounted in operating position in the mechanism 30. Valve 84 is positioned to occlude the outlet path 78 from pump chamber 74. Valve 86 is positioned to occlude outlet path 80 from pump chamber 76. Bladder inlet valves along pump chamber inlet paths 70 and 72 are identified by reference numerals 88 and 90, respectively. Valves 92 and 94 for controlling the passage of blood or crystalloid alternately to common inlet path 68 are positioned at inlets 64 and 66, respectively. Pump mechanism 30 is illustrated in Figure 3, and incorporates a pair of pumping motors 95 and 96. Pumping motor 95 is positioned to advance and retract a bladder driving element 98, and pumping motor 96 is positioned to similarly operate a second bladder driving element 100. Valve cam motor 102 is provided to operate all valve closures on the disposable cassette 26. Cam motor 102 turns an inlet cam shaft 104 carrying valve cams 106, 108, 110 and 112. Cam shaft 104 also turns, by means of pulleys 114 and 115 and timing belt 116, an outlet cam shaft 118. Outlet cam shaft 118 carries valving cams 120 and 122. As best seen in Figure 4, disposable cassette 26 is positioned tightly against the face of mechanism 30 by a closing door 124 so that the cassette bladder pumping chambers 74 and 76 are enclosed, and confront driving elements 98 and 100. Driving elements 98 and 100 may be of identical construction, and preferably of the petal module type disclosed in U.S. Patent 4,657,490, the disclosure of which is incorporated herein by reference. Although driving elements of this petal module type have the advantage of a linear relationship between displacement by the pump motor and volumetric displacement from the pump chamber, by their close compliance and confrontation to the plastic disposable cassette and by reduced shearing forces associated with the smooth pump action, other driving elements which provide a predictable volumetric displacement by a given advancement of the motor might be utilized. The petal module type of driving element illustrated includes a hub 130, surrounded by radially extending, pivotally mounted petals 132 so that the hub 130 together with the petals 132 provides a confronting surface for the confined pump chamber. Advancement of motor 95 or 96 causes its hub 130 to advance and carry the petals 132 along with it for reducing the volume of the confined pump chamber. Conversely, retraction of motor 95 or 96 causes the corresponding driving element 98 or 100 to retract, withdrawing the constraint on chamber volume. In Figure 4, element 98 is illustrated substantially fully retracted, so that pump chamber 74 is filled with fluid, and element 100 is pushed to its full advancement, emptying its pumping chamber 76. Means for measuring the force required to advance each motor, or a pressure sensor contacting the cassette 26 (not shown) is also provided to enable microprocessor 46 to record data representative of the pressure on each bladder chamber. Figure 5 illustrates the valving action embodied in mechanism 30, by showing the inlet and the outlet valve arrangement from a single pump chamber. All six valves (106, 108, 110, 112, 120 and 122) operate in similar fashion. Driving element 130 engages the disposable pump chamber 74. Inlet plunger valve 88A and outlet plunger valve 84A, controlled by cams 112 and 120 are normally closed by the action of biasing springs 134 and 136. In the closed condition dictated by the biasing springs, each valve plunger presses against its corresponding valve site on disposable cassette 26 closing the corresponding fluid path. The valve sites 84-94 are each provided with a similar, normally-closed valve. Each of the valve sites 84-94 is opened under the action of valve camming motor 102 upon rotation of its corresponding cam to an open position, retracting the valve plunger from the disposable cassette, and opening the corresponding flow path flow. In Figure 5, cam 112 has moved to the open position, retracting valve plunger 88A to open valve 88 on cassette 26, opening the inlet 70 of bladder 74 for entrance of fluid. Figure 6 illustrates the a timing diagram for the operation of the valve cam motor 102 in conjunction with the pumping motors 95 and 96. In the cycle described, one chamber pumps a mixture of blood and crystalloid in a selected ratio outwardly from outlet 82 of cassette 26, while the other pumping chamber is undergoing a sequential fill and test protocol. Filling chamber is filled with blood to the volume to produce the desired ratio followed by pressure testing of the chamber with its inlet and outlet valves closed to verified capture of the desired amount of blood. Following this step, the drive element of the filling pumping chamber is further retracted and crystalloid solution admitted to complete the filling of the chamber. Then the inlet and outlet valves on the filling chamber are closed to pressure test the chamber for a captured full load. Additional pressure tests and monitoring may be conducted during pumping to determine if there is any unsafe occlusion or to control the pressure within an appropriate safe range for a given procedure. Thus, at the commencement of the Figure 6 diagram, the pumping chamber bladder 74 has been emptied, and the other bladder 76 is full of a blood-crystalloid mixture in the desired proportions. The outlet valve 84, from chamber 74 is closed. Outlet valve 86 is open to pass the combined fluid from chamber 76 through the outlet 82 to the heat exchanger 31 at the requested volumetric flow rate. Throughout the period of delivery from chamber 76, its inlet valve 90 remains closed, and the corresponding pumping element 100 is advanced by motor 96 to reduce the volume of bladder 76 to expel the blood/crystalloid solution. The speed of motor 90 is governed by the requested flow rate. The outlet valve 84 from chamber 74 remains closed throughout this period of pumping from chamber 76. The valves 92 and 94 controlling inlet of blood and crystalloid to common inlet path 68, and the inlet valve for chamber 74 are sequentially opened and closed during the filling protocol for bladder 74, which occupies the time period during which bladder 76 is delivering fluid to line 28. Thus, when one bladder has completed its pumping step, the other has received solution constituents in the desired ratio and is ready to deliver. Substantially continuous flow is thus enabled. In the 4-step filling protocol for chamber 74, illustrated at the outset of the diagram, valves 92 and 88 are initially open, and valve 94 closed. Thus, an open flow path for entry of blood to chamber 74 is provided through inlet 64, common path 68 and pump chamber inlet path 70, while crystalloid is occluded at valve 94. Pump motor 95 is retracted sufficiently to admit sufficient blood to comprise the desired fraction of total chamber volume. Then valves 92 and 88 are closed, and pump motor 95 is advanced a few steps, to confirm by elevating pressure that the requested blood load has been captured between closed valves 88 and 94. With confirmed introduction of the correct amount of blood, valves 88 and 94 are opened while valve 92 remains closed to stop further blood entry. The pump motor 95 now retracts to admit the correct volume of crystalloid along paths 66, 68 and 70. This is followed by closing valves 88 and 94. Motor 95 is advanced briefly to confirm by pressure elevation that the full incremental volume has been occupied by crystalloid solution. With this confirmation, the fill protocol is complete, and chamber 74 is ready for delivery on the completion of delivery from chamber 76. As chamber 74 then delivers, chamber 76 undergoes a similar 4-step filling protocol. It will be appreciated that a change in blood/crystalloid ratio is a simple adaptation for the pump mechanism 30. In the diagram, the retraction of the pumping element during blood fill and crystalloid fill is depicted as substantially equal. If a different ratio is requested through control panel 52, microprocessor 46 simply directs the motors 95 and 96 to retract by different amounts during their blood-fill and crystalloid-fill steps. The full retraction of a motor is the same for the combined fill. It is simply necessary to adjust the amount of retraction during each fill step to the requested ratio. The ratio may be continuously adjusted from 100% of blood to 100% crystalloid. Thus, if the requested blood/crystalloid ratio is R, and the motor driven-volume displacement relationship is linear, R = Number of motor steps retracted during blood fill Number of motor steps retracted during crystalloid fill The total volumetric flow rate from the cassette is varied pursuant to operator request simply by compressing or expanding the time for a cycle to be completed. Of course, if intermittent operation is desired, this may be provided as well. No matter what changes may be made to the blood/crystalloid flow rate, microprocessor 46 preferably automatically controls potassium pump 32 to deliver at a ratio which provides the requested percentage of the blood/crystalloid flow. The improved and simplified control over cardioplegia enabled by this invention, and improved solution handling, are believed to represent a significant tool specifically for the heart surgeon/perfusionist team, as well as for other healthcare teams which may require controlled pumping or recirculation of blood mixed with one or more other fluids. Although the present invention has been described with respect to specific embodiments thereof, it will be understood that various changes and modifications will be suggested to one skilled in the art and it is intended to encompass such changes and modifications as fall within the scope of the appended claims.

Claims: A cardioplegia system to deliver cardioplegic solution to a heart during open heart surgery in cooperation with an extracorporeal blood circuit having an oxygenator (14), the cardioplegia system having a conduit (12) to divert a first fluid portion to the cardioplegic system from a first fluid flow originating from the oxygenator (14), a cardioplegic fluid line (28), a first pump (30) to pump the first fluid portion and a second fluid obtained from a second source (24) into the cardioplegic fluid line (28), a second pump (32) to pump a third fluid into the cardioplegic fluid line (28), and a heat exchanger (31) to control a fluid temperature of a fluid mixture in the cardioplegic fluid line (28), characterized in that : (a) the third fluid is introduced into the cardioplegic fluid line (28) at a flow rate less than about 10% of an output flow rate from the first pump (30); and (b) the system further comprises a controller (46) to adjust a volumetric rate of flow from the first pump (30) and to control operations of the second pump (32) so that a volumetric rate of flow of the third fluid is automatically maintained at a selected percentage of the volumetric rate of flow from the first pump (30), at all adjusted volumetric rates of flow from the first pump (30), by automatically resetting the volumetric rate of flow from the second pump (32) to the selected percentage of the volumetric rate of flow from the first pump (30) upon a change in the volumetric rate of flow from the first pump (30). A cardioplegia system as in Claim 1, wherein the first pump (30) is adapted to deliver the first fluid and the second fluid to the cardioplegia fluid line (28) in a variable ratio. A cardioplegia system as in Claim 1, wherein the heat exchanger (31), coupled to the cardioplegia fluid line (28), has mechanisms (33, 34, 36, 38, 40) for both heating and cooling output of the first pump (30), and the controller (46) is coupled to the heat exchanger (31) to effect such heating and cooling. A cardioplegia system as in Claim 1, wherein the first pump (30) comprises a pump chamber (74) having an inlet (68), an outlet (82), and a drive (95, 130) to vary a volume of the pump chamber (74). A cardioplegia system as in Claim 4, wherein the first pump (30) has two pumping chambers (74, 76), so that one chamber may be refilled while the other is emptying, whereby operationally continuous flow from the first pump (30) may be achieved. A cardioplegia system as in Claim 4, wherein at least the first pump (30) receives a disposable component (26) through which fluid flows. A cardioplegia system as in Claim 4, wherein the controller (46) is coupled to the drive (95, 130) to control a fill cycle of the pump chamber (74), whereby the fill cycle comprises two separate time segments including a first period for introduction of the first fluid from the first source (14) and a second period for introduction of the second fluid from the second source (24), whereby the first fluid and the second fluid are combined in the pump chamber (74) in a selected ratio before being expelled from the first pump (30). A cardioplegia system as in Claim 1, wherein the controller (46) further monitors a fluid pressure of the volumetric rate of flow from the first pump (30). A cardioplegia system as in Claim 1, upon selection by a user of a volumetric flow rate of the first pump (30), the controller (46) establishes the flow rate of the second pump (32). A cardioplegia system to deliver cardioplegic solution, such solution having a first fluid and a second fluid that is adapted to inhibit heart activity, to a heart during open heart surgery in cooperation with an extracorporeal blood circuit having an oxygenator (14), the cardioplegia system having a conduit (12) to divert a first fluid portion to the cardioplegic system from a first fluid flow originating from the oxygenator (14), a cardioplegic fluid line (28), a first pump (30) to pump the first fluid portion into the cardioplegic fluid line (28), a second pump (32) to pump the second fluid into the cardioplegic fluid line (28), and a heat exchanger (31) to control a fluid temperature of a fluid mixture in the cardioplegic fluid line (28), characterized in that : (a) a flow rate of an output from the first pump is variable from 0 ml/min to 500 ml/min; (b) the second fluid is introduced into the cardioplegic fluid line (28) at a flow rate less than about 10% of an output flow rate from the first pump (30), and (c) the cardioplegic system further includes a controller (46) to adjust a volumetric rate of flow from the first pump (30) and to control operations of the second pump (32) so that a volumetric rate of flow of the second fluid is automatically maintained at a selected percentage of the volumetric rate of flow from the first pump (30) at all adjusted volumetric rates of flow from the first pump (30) by automatically resetting the volumetric rate of flow from the second pump (32) to the selected percentage of the volumetric rate of flow from the first pump (30) upon a change in the volumetric rate of flow from the first pump (30). A cardioplegia system as in Claim 10, wherein the heat exchanger (31), coupled to the cardioplegia fluid line (28), has mechanisms (33, 34, 36, 38, 40) for both heating and cooling output of the first pump (30), and the controller (46) is coupled to the heat exchanger (31) to effect such heating and cooling. A cardioplegia system as in Claim 10, wherein the first pump (30) comprises a pump chamber (74) having an inlet (68), an outlet (82), and a drive (95, 130) to vary a volume of the pump chamber (74). A cardioplegia system as in Claim 12, wherein the first pump (30) has two pumping chambers (74, 76), so that one chamber may be refilled while the other is emptying, whereby operationally continuous flow from the first pump (30) may be achieved. A cardioplegia system as in Claim 12, wherein at least the first pump (30) receives a disposable component (26) through which fluid flows. A cardioplegia system as in Claim 12, wherein the controller (46) is coupled to the drive (95, 130) to control a fill cycle of the pump chamber (74), whereby the fill cycle comprises two separate time segments including a first period for introduction of the first fluid from the first source (14) and a second period for introduction of the second fluid from the second source (24), whereby the first fluid and the second fluid are combined in the pump chamber (74) in a selected ratio before being expelled from the first pump (30). A cardioplegia system as in Claim 10, wherein the controller (46) further monitors a fluid pressure of the volumetric rate of flow from the first pump (30). A cardioplegia system as in Claim 10, upon selection by a user of a volumetric flow rate of the first pump (30), the controller (46) establishes the flow rate of the second pump (32).

Inventors: ABBOTT MARTYN, DAVIS ALBERT M, JONES KENNETH A, MATTSON ANDREW P, THOMPSON THOMAS C, ABBOTT, MARTYN, DAVIS, ALBERT M., JONES, KENNETH A., MATTSON, ANDREW P., THOMPSON, THOMAS C.
Applicants: QUEST MEDICAL INC, QUEST MEDICAL, INC.
Application year: 1994
Main classification: A61M1
IPC codes: A61M5, A61M1, F04B43, A61M19